Three element coaxial vaso-occlusive device

ABSTRACT

A vaso-occlusive device includes inner, intermediate, and outer elements arranged coaxially. The inner element is a filamentous element, preferably a microcoil. The intermediate element is made of a non-metallic material, preferably an expansile polymer. The outer element is substantially non-expansile and defines at least one gap or opening through which the intermediate element is exposed. In a preferred embodiment, when the intermediate element is expanded, it protrudes through the at least one gap or opening in the outer element and assumes a configuration with an undulating, convexly-curved outer surface defining a chain of arcuate segments, each having a diameter significantly greater than the diameter of the outer element. The expanded configuration of the intermediate element minimizes friction when the device is deployed through a microcatheter, thereby reducing the likelihood of buckling while maintaining excellent flexibility. The result is a device with enhanced pushability and trackability when deployed through a microcatheter.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. patent application Ser. No.10/631,981 filed Jul. 31, 2003 now U.S. Pat. No. 8,273,100 entitledThree Element Coaxial Vaso-Occlusive Device, which claims the benefit,under 35 U.S.C. Section 119(e), of U.S. Provisional Application Ser. No.60/400,013, filed Jul. 31, 2002 entitled Three Layer CoaxialVaso-Occlusive Device, both of which are incorporated herein byreference in their entireties.

FEDERALLY-SPONSORED RESEARCH OR DEVELOPMENT

Not Applicable

BACKGROUND

This invention relates to vaso-occlusive devices, such as vaso-occlusivecoils and the like, for the embolization of vascular aneurysms andsimilar vascular abnormalities. Specifically, the invention is animprovement over existing two layer or two element coaxialvaso-occlusive devices, particularly those having a polymer coating orcovering. In particular, the present invention is a three layer or threeelement coaxial vaso-occlusive device that provides improved durability,pushability, and trackability inside a microcatheter. The characteristictermed “trackability” relates to the ease of advancing oneinterventional device within or over another, and it is related tofriction and flexibility.

Vaso-occlusive devices are typically used within the vasculature of thehuman body to block the flow of blood through a vessel through theformation of an embolus. Vaso-occlusive devices are also used to form anembolus within an aneurysm stemming from the vessel. Vaso-occlusivedevices can be formed of one or more elements, generally delivered intothe vasculature via a catheter or similar mechanism.

The embolization of blood vessels is desired in a number of clinicalsituations. For example, vascular embolization has been used to controlvascular bleeding, to occlude the blood supply to tumors, and to occludevascular aneurysms, particularly intracranial aneurysms. In recentyears, vascular embolization for the treatment of aneurysms has receivedmuch attention. Several different treatment modalities have beenemployed in the prior art. One approach that has shown promise is theuse of thrombogenic microcoils. These microcoils may be made of abiocompatible metal alloy (typically platinum and tungsten) or asuitable polymer. If made of metal, the coil may be provided with Dacronfibers to increase thrombogenicity. The coil is deployed through amicrocatheter to the vascular site. Examples of microcoils are disclosedin the following U.S. Pat. No. 4,994,069—Ritchart et al.; U.S. Pat. No.5,133,731—Butler et al.; U.S. Pat. No. 5,226,911—Chee et al.; U.S. Pat.No. 5,312,415—Palermo; U.S. Pat. No. 5,382,259—Phelps et al.; U.S. Pat.No. 5,382,260—Dormandy, Jr. et al.; U.S. Pat. No. 5,476,472—Dormandy,Jr. et al.; U.S. Pat. No. 5,578,074—Mirigian; U.S. Pat. No.5,582,619—Ken; U.S. Pat. No. 5,624,461—Mariant; U.S. Pat. No.5,645,558—Horton; U.S. Pat. No. 5,658,308—Snyder; and U.S. Pat. No.5,718,711—Berenstein et al.

A specific type of microcoil that has achieved a measure of success isthe Guglielmi Detachable Coil (“GDC”), described in U.S. Pat. No.5,122,136—Guglielmi et al. The GDC employs a platinum wire coil fixed toa stainless steel delivery wire by a solder connection. After the coilis placed inside an aneurysm, an electrical current is applied to thedelivery wire, which electrolytically disintegrates the solder junction,thereby detaching the coil from the delivery wire. The application ofthe current also creates a positive electrical charge on the coil, whichattracts negatively-charged blood cells, platelets, and fibrinogen,thereby increasing the thrombogenicity of the coil. Several coils ofdifferent diameters and lengths can be packed into an aneurysm until theaneurysm is completely filled. The coils thus create and hold a thrombuswithin the aneurysm, inhibiting its displacement and its fragmentation.

The advantages of the GDC procedure are the ability to withdraw andrelocate the coil if it migrates from its desired location, and theenhanced ability to promote the formation of a stable thrombus withinthe aneurysm.

A more recent development in the field of microcoil vaso-occlusivedevices is exemplified in U.S. Pat. No. 6,299,619—Greene, Jr. et al. andU.S. Pat. No. 6,602,261—Greene, Jr. et al., both assigned to theassignee of the subject invention. These patents disclose vaso-occlusivedevices comprising a microcoil with one or more expansile elementsdisposed on the outer surface of the coil. The expansile elements may beformed of any of a number of expansile polymeric hydrogels, oralternatively, environmentally-sensitive polymers that expand inresponse to a change in an environmental parameter (e.g., temperature orpH) when exposed to a physiological environment, such as the bloodstream.

While the microcoils with expansile elements have exhibit great promisein, for example, embolizing aneurysms of a wide variety of sizes andconfigurations, the expansile elements increase the frictional forcesbetween the vaso-occlusive device and a microcatheter through which thedevice is deployed. Furthermore, depending on the configuration andmaterial of the expansile elements, the flexibility of the device may bereduced. These factors may result in a device that has less than optimalpushability (resistance to buckling) and reduced trackability (asdefined above).

There has thus been a long-felt, but as yet unsatisfied need for amicrocoil vaso-occlusive device that has all the advantages of theexpansile element type of device, and that also exhibits enhancedpushability and trackability, with good durability characteristics.

SUMMARY OF THE INVENTION

Broadly, the present invention is a vaso-occlusive device, comprisingthree coaxial elements: an elongate, flexible, filamentous innerelement; a non-metallic intermediate element coaxially surrounding theinner element and in intimate contact therewith; and an outer elementcoaxially surrounding the intermediate element and in intimate contacttherewith, the outer element including one or more openings or gapsthrough which the intermediate element is exposed.

In a preferred embodiment of the invention, the inner element is in theform of a helical coil made of a biocompatible, radiopaque metal, andthe intermediate element is a conformal coating or layer on the innerelement, the conformal coating or layer being made of a soft polymericmaterial that is preferably an expansile polymer. Advantageously, thepolymeric hydrogel is an environmentally-responsive hydrogel thatexpands upon exposure to the physiological environment, for example, ofthe blood stream. The polymer may advantageously be bio-absorbable orbiodegradable. Also in the preferred embodiment, the outer element is ahelical “over-coil” that is loosely wound (“open-wound”) over theintermediate element, except at proximal and distal end sections, whereit is tightly wound (“close-wound”). The close-wound proximal and distalend sections support the inner element, protecting it from damage duringdeployment and any necessary repositioning, while also securely bindingthe intermediate element to the inner element at the proximal and distalends of the device and restraining the hydrogel of the intermediateelement from expanding at the respective ends of the device. Theopen-wound section between the proximal and distal end sections createsa single, continuous helical opening through which the intermediateelement expands. The helical configuration of the opening forces theexpanded polymeric intermediate element to assume the configuration of achain of arcuate segments protruding radially outwardly between thecoils of the over-coil, rather than that of a continuous polymeric layerhaving a continuous, uninterrupted exterior surface. Because each of thearcuate segments contacts the interior surface of a microcatheter (e.g.,during deployment) primarily at or near a tangential contact point, thetotal contact area of the intermediate element is reduced as compared toa continuous axial polymeric element. This reduced contact areacorrespondingly reduces the aggregate friction between the polymericlayer and the microcatheter, thereby decreasing the resistance tomanipulation of the device. The open-wound section also creates hingepoints between the arcuate segments of the polymeric intermediateelement, thereby increasing the overall flexibility of the device.

It has been confirmed experimentally that the reduced friction andincreased flexibility afforded by the outer element, and by theinteraction between the outer and intermediate elements, enhances theboth the pushability and trackability of a device made in accordancewith the present invention, as compared, for example, with prior artmicrocoil devices having expansile polymeric coatings or elements on oralong their exterior surfaces.

The invention thus provides a microcoil vaso-occlusive device with anexpansile element that allows the device to embolize very efficiently awide variety of vascular abnormalities, e.g., aneurysms of a widevariety of shapes, sizes, and locations, and yet that exhibits enhancedpushability and trackability as compared to the prior art.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a vaso-occlusive device in accordancewith a preferred embodiment of the present invention;

FIG. 2 is an axial cross-sectional view of the device of FIG. 1;

FIG. 3 is a perspective view, similar to that of FIG. 1, showing theexpansile polymeric intermediate element in its expanded state;

FIG. 4 is an axial cross-sectional view of FIG. 3; and

FIG. 5 is a perspective view of an alternative embodiment of theinvention.

DESCRIPTION OF THE INVENTION

Referring to FIGS. 1-4, a vaso-occlusive device 10, in accordance with apreferred embodiment of the invention, comprises three elongate, coaxialelements: an inner core element 11, a non-metallic intermediate element12, and a non-expansile outer element 13 that covers at least a portionof the intermediate element. The intermediate element 12 is in intimatecontact with both the inner element 11 and the outer element 13.

The inner element 11 is formed of a flexible, elongate filament or wirethat is preferably made of a material that allows visualization undervarious medical imaging means, such as X-ray, MRI, or ultrasound.Preferably, the inner element 11 is formed from a length of wire made ofany of various biocompatible, radiopaque metals, such as platinum,tantalum, tungsten, gold, titanium, nitinol, stainless steel, Elgiloy(cobalt-chromium-nickel), or other suitable alloys known in the art.Alternatively, it can be made from or include non-metallic materials,such polymers, collagen, proteins, drugs, and biologic materials,bioactive agents, therapeutic compounds, or combinations of thesematerials. If made of a non-radiopaque material, it shouldadvantageously be doped or impregnated or chemically modified to bevisible with one or more imaging techniques. Alternatively, it can bemade of a material that is highly visible by means of MRI or ultrasound.The inner element 11 can be formed in various configurations, including,but not limited to, coils, rods, tubes, cables, braids, cut tubes, orother elongate, flexible forms. As shown, it is in the form of a helicalcoil, which may be preferred. In one specific embodiment, it is formedat least in part of a multi-filar coil configuration, as described inthe co-owned and co-pending U.S. application Ser. No. 10/189,934; filedJul. 2, 2002, the disclosure of which is incorporated herein byreference.

The intermediate element 12 may be formed as a coating, wrapping,tubular sleeve, or other construction to create a substantiallycontinuous surface coaxially around the inner element 11. Alternatively,it can be formed into a cylinder and then skewered onto the inner coreelement 11, as described in the co-owned and co-pending U.S. applicationSer. No. 10/157,621; filed May 29, 2002, the disclosure of which isincorporated herein by reference. The intermediate element 12 preferablycovers all of the length of the inner element 11, except for shortproximal and distal sections.

The intermediate element 12 may be made of any of various suitable,substantially non-metallic, biocompatible materials, including polymers,biopolymers, biologic materials, and combinations of these materials.Suitable polymers include cellulose, polypropylene,polyvinylpyrrolidone, polyacrylics, polylactides, polyamides, polyvinylalcohol, polyester, polyurethane, polyglycolic acid, polyfluorocarbons,hydrogels, and silicones. Exemplary biologic materials includealginates, hyaluronic acid, fibrin, collagen and silk. Optionally, theintermediate element 12 can be impregnated, grafted, bound, or modifiedto deliver therapeutic compounds, proteins, genes, bioactive agents, orcellular material. See, e.g., U.S. Pat. No. 5,658,308 and InternationalPublications Nos. WO 99/65401 and WO 00/27445, the disclosures of whichare incorporated herein by reference. In one preferred embodiment, theintermediate element 12 is made of a state-of-the-art bioabsorbable orbiodegradable polymer, such as, for example, those described in USPublished Applications Nos. 2002/0040239 and 2002/0020417, thedisclosures of which are incorporated herein by reference. In anotherpreferred embodiment, the intermediate element 12 is made of a softconformal material, and more preferably of an expansile material such asa hydrogel.

The most preferred material is an environmentally responsive hydrogel,such as that described in co-owned and co-pending U.S. application Ser.No. 09/804,935, the disclosure of which is incorporated herein byreference. Specifically, the hydrogels described in application Ser. No.09/804,935 are of a type that undergoes controlled volumetric expansionin response to changes in such environmental parameters as pH ortemperature. These hydrogels are prepared by forming a liquid mixturethat contains (a) at least one monomer and/or polymer, at least aportion of which is sensitive to changes in an environmental parameter;(b) a cross-linking agent; and (c) a polymerization initiator. Ifdesired, a porosigen (e.g., NaCl, ice crystals, or sucrose) may be addedto the mixture, and then removed from the resultant solid hydrogel toprovide a hydrogel with sufficient porosity to permit cellular ingrowth.The controlled rate of expansion is provided through the incorporationof ethylenically unsaturated monomers with ionizable functional groups(e.g., amines, carboxylic acids). For example, if acrylic acid isincorporated into the crosslinked network, the hydrogel is incubated ina low pH solution to protonate the carboxylic acids. After the excesslow pH solution is rinsed away and the hydrogel dried, the hydrogel canbe introduced through a microcatheter filled with saline atphysiological pH or with blood. The hydrogel cannot expand until thecarboxylic acid groups deprotonate. Conversely, if an amine-containingmonomer is incorporated into the crosslinked network, the hydrogel isincubated in a high pH solution to deprotonate amines. After the excesshigh pH solution is rinsed away and the hydrogel dried, the hydrogel canbe introduced through a microcatheter filled with saline atphysiological pH or with blood. The hydrogel cannot expand until theamine groups protonate.

More specifically, in a preferred formulation of the hydrogel, themonomer solution is comprised of ethylenically unsaturated monomers, anethylenically unsaturated crosslinking agent, a porosigen, and asolvent. At least a portion, preferably 10%-50%, and more preferably10%-30%, of the monomers selected must be pH sensitive. The preferred pHsensitive monomer is acrylic acid. Methacrylic acid and derivatives ofboth acids will also impart pH sensitivity. Since the mechanicalproperties of hydrogels prepared exclusively with these acids are poor,a monomer to provide additional mechanical properties should beselected. A preferred monomer for providing mechanical properties isacrylamide, which may be used in combination with one or more of theabove-mentioned pH sensitive monomers to impart additional compressivestrength or other mechanical properties. Preferred concentrations of themonomers in the solvent range from 20% w/w to 30% w/w.

The crosslinking agent can be any multifunctional ethylenicallyunsaturated compound, preferably N, N′-methylenebisacrylamide. Ifbiodegradation of the hydrogel material is desired, a biodegradablecrosslinking agent should be selected. The concentrations of thecrosslinking agent in the solvent should be less than about 1% w/w, andpreferably less than about 0.1% w/w.

The porosity of the hydrogel material is provided by a supersaturatedsuspension of a porosigen in the monomer solution. A porosigen that isnot soluble in the monomer solution, but is soluble in the washingsolution can also be used. Sodium chloride is the preferred porosigen,but potassium chloride, ice, sucrose, and sodium bicarbonate can also beused. It is preferred to control the particle size of the porosigen toless than about 25 microns, more preferably less than about 10 microns.The small particle size aids in the suspension of the porosigen in thesolvent. Preferred concentrations of the porosigen range from about 5%w/w to about 50% w/w, more preferably about 10% w/w to about 20% w/w, inthe monomer solution. Alternatively, the porosigen can be omitted and anon-porous hydrogel can be fabricated.

The solvent, if necessary, is selected based on the solubilities of themonomers, crosslinking agent, and porosigen. If a liquid monomer (e.g.2-hydroxyethyl methacrylate) is used, a solvent is not necessary. Apreferred solvent is water, but ethyl alcohol can also be used.Preferred concentrations of the solvent range from about 20% w/w toabout 80% w/w, more preferably about 50% w/w to about 80% w/w.

The crosslink density substantially affects the mechanical properties ofthese hydrogel materials. The crosslink density (and hence themechanical properties) can best be manipulated through changes in themonomer concentration, crosslinking agent concentration, and solventconcentration. The crosslinking of the monomer can be achieved throughreduction-oxidation, radiation, and heat. Radiation crosslinking of themonomer solution can be achieved with ultraviolet light and visiblelight with suitable initiators or ionizing radiation (e.g. electron beamor gamma ray) without initiators. A preferred type of crosslinkinginitiator is one that acts via reduction-oxidation. Specific examples ofsuch red/ox initiators that may be used in this embodiment of theinvention are ammonium persulfate andN,N,N′,N′-tetramethylethylenediamine.

After the polymerization is complete, the hydrogen is washed with water,alcohol or other suitable washing solution(s) to remove theporosigen(s), any unreacted, residual monomer(s) and any unincorporatedoligomers. Preferably this is accomplished by initially washing thehydrogel in distilled water.

As discussed above, the control of the expansion rate of the hydrogel isachieved through the protonation/deprotonation of ionizable functionalgroups present on the hydrogel network. Once the hydrogel has beenprepared and the excess monomer and porosigen have been washed away, thesteps to control the rate of expansion can be performed.

In embodiments where pH sensitive monomers with carboxylic acid groupshave been incorporated into the hydrogel network, the hydrogel isincubated in a low pH solution. The free protons in the solutionprotonate the carboxylic acid groups on the hydrogel network. Theduration and temperature of the incubation and the pH of the solutioninfluence the amount of control on the expansion rate. Generally, theduration and temperature of the incubation are directly proportional tothe amount of expansion control, while the solution pH is inverselyproportional. It has been determined that the water content of thetreating solution also affects the expansion control. In this regard,the hydrogel is able to expand more in the treating solution and it ispresumed that an increased number of carboxylic acid groups areavailable for protonation. An optimization of water content and pH isrequired for maximum control on the expansion rate. After the incubationis concluded, the excess treating solution is washed away and thehydrogel material is dried. The hydrogel treated with the low pHsolution has been observed to dry down to a smaller dimension than theuntreated hydrogel. This is a desired effect since delivery of thesehydrogel materials through a microcatheter is desired.

If pH sensitive monomers with amine groups were incorporated into thehydrogel network, the hydrogel is incubated in high pH solution.Deprotonation occurs on the amine groups of the hydrogel network at highpH. The duration and temperature of the incubation, and the pH of thesolution, influence the amount of control on the expansion rate.Generally, the duration, temperature, and solution pH of the incubationare directly proportional to the amount of expansion control. After theincubation is concluded, the excess treating solution is washed away andthe hydrogel material is dried.

For the embodiment of the vaso-occlusive device having an intermediateelement formed of an expansile polymeric hydrogel, when the intermediateelement 12 expands, the areas of the soft, conformal intermediateelement 12 that are not covered or constrained by the outer element 13extend radially outward through the openings or gaps, or between thecoils of the outer element 13 (as described below) to form an undulatingouter surface comprising a chain of arcuate segments, as a result of theconstraint imposed by the outer element 13. Because the arcuate segmentsof the undulating outer surface contact the interior wall surface of amicrocatheter through which the device is deployed only at or neartangential contact points proximate the apex of each segment, thisundulating or arcuate configuration provides reduced friction ascompared to a continuous or smooth surface of the same material.

The outer element 13 is a flexible, elongate, substantially tubularmember, at least a substantial portion of the length of which, andpreferably most of the length of which, includes or defines at least oneopening or gap to allow the exposure and/or protrusion of theintermediate element 12. Suitable configurations for the outer element13 include helical coils, braids, and slotted or spiral-cut tubes. Theouter element 13 may be made of any suitable biocompatible metal orpolymer, including those listed above for the inner element 11. Forthose embodiments using a soft, conformal intermediate element 12, theouter element 13 should have sufficient radial strength to compress orrestrain the intermediate element 12.

In the most preferred embodiment, the device comprises an inner coreelement 11 formed of a tightly-wound (“close-wound”) helical coil of abiocompatible metal wire (e.g., platinum alloy), an intermediate element12 of a hydrophilic expansile polymer (e.g., hydrogel), and an outerelement 13 in the form of a biocompatible metal or polymer helical coilthat is open-wound for most of its length, with a close-wound proximalend section 14 and a close-wound distal end section 15. The open-woundportion of the outer element defines a single, continuous, helicalopening or gap. A coupling element 16 is advantageously attached to theproximal end of the inner element 11 for detachable attachment to adeployment device (not shown). A rounded distal obturator tip 17 may beattached to the distal end of the inner element 11.

In the above-described most preferred embodiment, the hydrogel of theintermediate element 12 expands or swells upon exposure to an aqueousenvironment (e.g., blood). Preferably, the hydrogel expands to betweenabout two times and about 20 times its original volume. As shown inFIGS. 3 and 4, the swollen or expanded intermediate element 12 protrudesthrough the helical opening or gap defined between the coils of theopen-wound section of the outer element 13 to form an undulating,convexly-curved surface defining a chain of arcuate or rounded segments,each having a diameter that is substantially greater than the diameterof the outer element 13. The open-wound section of the coil forming theouter element 13 preferably has a coil pitch that is at least one-halfthe diameter of the outer element 13. The coil is preferably made from awire that has a diameter of no more than about 0.15 mm.

The helical outer element 13 described above may be considered asdefining a single, helical opening or gap, or it may be viewed asdefining a plurality of connected openings or gaps, each defined betweenan adjacent pair of windings of the coil of the outer element 13.Alternatively, if the outer element 13 is formed as a slotted tube, forexample, the outer element 13 will be seen to define a plurality ofdiscrete openings or gaps in its axial middle section that arefunctionally equivalent to the helical opening(s) defined in theillustrated embodiment.

The device 10 can be constructed with various radial thickness of eachcoaxial element to provide different handling characteristics.Preferably, the inner element 11 has a diameter of between about 0.075mm and 0.75 mm; the intermediate element 12 has a thickness of betweenabout 0.025 mm and 1.00 mm; and the outer element 13 has a thickness ofbetween about 0.025 mm and 0.25 mm. For the embodiments that use anexpansile intermediate element 12, these thicknesses are measured in thenon-expanded state. Preferably, the outer diameter of the outer element13 is actually somewhat less than the expanded or swollen diameter ofthe intermediate element 12, so that the latter will readily expandthrough the openings or gaps in the outer element 13.

FIG. 5 shows a vaso-occlusive device 10′ in accordance with analternative embodiment of the invention. This embodiment includes anouter element 13′ with a distal section 15′ that is not close wound, butis, instead, made with small gaps of approximately 5% to 100% of thediameter of the wire or filament of which the outer element 13′ is made.These gaps make the distal section 15′ of the device 10′ more flexiblein the area where the outer element 13′ overlaps the inner element 11′.

In the embodiment shown in FIG. 5, the proximal ends of both the innerelement 11′ and the outer element 13′ are both advantageously attachedto a coupling element 16′ by soldering or welding. The attachment ofboth the inner element 11′ and the outer element 13′ to the couplingelement 16′ makes the proximal end of the device 10′ more resistant todeformation during deployment and implantation.

As indicated above, the present invention provides good trackability ina microcatheter. In other words, it is easily advanced through acatheter without binding against or moving the catheter. This advantageis achieved through reduced friction and reduced buckling at the ends ofthe device. The force required to advance the device through a typicalmicrocatheter would normally be less than about 0.7 lbs.

The device is preferably detachable from a flexible, elongate deliveryapparatus (not shown), such as a wire, a pusher tube, or the like.Exemplary detachment systems known in the art include electrolytic,mechanical, electromechanical, thermal, ultrasonic, and hydraulicdetachment mechanisms. The device may be formed into a secondaryconfiguration, such as a helical coil, a sphere, an ovoid, or any othersuitable two- or three-dimensional shape known in the art ofvaso-occlusive devices. Alternatively, the device can be left in arelatively straight configuration with or without a curvature at the endsuch as a “J” configuration).

The device is useful for the occlusion and/or embolization of bloodvessels, other vascular spaces such as aneurysms, and other tubular orsaccular organs or spaces throughout the body. Specific applicationswhere it may be useful include the occlusion of cerebral aneurysms,aortic aneurysms, fistulas, fallopian tubes, cardiac septal defects,patent foramen ovale, and the left atrial appendage of the heart. Forsome of these applications, it may be preferable to use devices withdimensions larger than those specified above.

Although preferred embodiments of the invention have been described inthis specification and the accompanying drawings, it will be appreciatedthat a number of variations and modifications may suggest themselves tothose skilled in the pertinent arts. Thus, the scope of the presentinvention is not limited to the specific embodiments and examplesdescribed herein, but should be deemed to encompass alternativeembodiments and equivalents, as determined by a fair reading of theclaims that follow.

The invention claimed is:
 1. A method of occluding a body cavity,comprising: delivering an implant to a vascular abnormality of a bodycavity with a delivery device, said implant comprising an open-coiledelement surrounding a hydrogel element and defining a gap; expandingsaid hydrogel element through said gap within said vascular abnormalityat a controlled rate in response to an environmental parameter; and,detaching said implant from said delivery device.
 2. The method of claim1, wherein said hydrogel element surrounds a microcoil.
 3. The method ofclaim 1, further comprising detaching a coupling element from a proximalend of said implant.
 4. The method of claim 1, wherein saidenvironmental parameter is temperature.
 5. The method of claim 1,wherein said environmental parameter is pH.
 6. The method of claim 1,wherein said expanding said hydrogel element at a controlled rate inresponse to an environmental parameter further comprises expanding saidhydrogel element through gaps of said open-coiled element to form anexterior surface having an undulating configuration defining a chain ofconvexly-curved arcuate segments.
 7. The method of claim 1, wherein saidopen-coiled element comprises a wire forming a helical configuration. 8.The method of claim 1, wherein said hydrogel element expandsvolumetrically.
 9. A method of occluding a body cavity, comprising:providing an implant; said implant having a first flexible hydrogelelement coaxially located within a second flexible element; deliveringsaid implant with a delivery device to a vascular abnormality; exposingsaid first flexible hydrogel element to fluid through gaps defined bysaid second flexible element; detaching said implant from said deliverydevice; and, allowing said first flexible hydrogel element to expand ata controlled rate within said second element responsive to anenvironmental parameter of said fluid.
 10. The method of claim 9,further comprising a microcoil located within said first flexiblehydrogel element and made of a biocompatible material selected from agroup consisting of metal wire and polymeric filament.
 11. The method ofclaim 9, further comprising expanding said first flexible hydrogelelement through said gaps defined by said second flexible member. 12.The method of claim 9, wherein said second flexible element comprises anopen-wound, helically-coiled wire.
 13. The method of claim 9, whereinsaid first flexible hydrogel element has a rate of expansion responsiveto a change in temperature or pH.
 14. The method of claim 9, furthercomprising uncoupling a proximal end of said implant.
 15. Avaso-occlusive device implantable in a vascular abnormality, comprising:an expansile first hydrogel member expandable at a controlled rate inresponse to an environmental parameter; a second member helicallysurrounding said first hydrogel member and defining a gap through whichthe first hydrogel member is exposed; and, wherein said vaso-occlusivedevice is selectively detachable from a delivery device within apatient.
 16. The vaso-occlusive device of claim 15, wherein saidenvironmental parameter is pH.
 17. The vaso-occlusive device of claim15, wherein said environmental parameter is temperature.
 18. Thevaso-occlusive device of claim 15, wherein said second member is anopen-wound helical coil defining said gap.
 19. The vaso-occlusive deviceof claim 15, further comprising a third member located within saidexpansile first hydrogel member, and wherein said third member is amicrocoil.
 20. A vaso-occlusive device implantable in a vascularabnormality, comprising: an open-coiled element; an expansile hydrogelelement exposed between loops of said open-coiled element and expandableat a controlled rate against said open-coiled element; and, wherein saidvaso-occlusive device is selectively detachable from a delivery devicewithin a patient.
 21. The vaso-occlusive device of claim 20, whereinsaid expansile hydrogel element volumetrically expands at a controlledrate in response to an environmental parameter.
 22. The vaso-occlusivedevice of claim 21, wherein said environmental parameter is pH ortemperature.